Device for direct electrical detection of molecules and molecule-molecule interactions

ABSTRACT

An analysis device includes an electrode arrangement, a current/voltage provider, and a circuit analyzer. The electrode arrangement has an interdigitated electrode pair including a first electrode and a second electrode. Coupled to the electrode arrangement is a signal generator adapted to provide a signal (e.g., an alternating current or voltage) having a selected range of frequencies. The analyzer is coupled to the electrode arrangement and is operative to analyze an electrical parameter of the circuit as the signal is applied. An analytic method includes measuring changes in one or more parameters of the circuit over the range of frequencies. By such measurement, the device can determine whether a target moiety has been bound by a probe attached to the electrode(s). The device can also specifically identify the intermolecular system detected, i.e., by “finger-printing” the electrical response of each molecule or intermolecular complex.

BACKGROUND OF THE INVENTION

The present invention is related to the field of bioelectrical circuitanalyzers, and more specifically to bioelectrical circuit analyzerscapable of identifying and categorizing various biomolecules andbiomolecular complexes by electrical parameter analysis thereof.

Detection of antigens such as viruses and bacteria is critical formedical diagnoses. Currently, the commonly used methods forimmunological tests include enzyme-linked immunosorbent assay (ELISA)and immunoradiometric assay (IRMA). However, these multi-step techniquestend to be tedious and expensive. Hence, there is considerable effortdirected towards development of microsensors, in particularimmunosensors that can allow quick and precise detection of molecules.

Identification of biomolecular complexes also is advantageous inresearch, e.g. pharmaceutical research and development. As one example,a gene regulatory protein can be identified by its ability to bind to aspecific deoxyribonucleic acid sequence. Current methods for detectingsuch complexes include radiometric, fluorometric and chromogenic assays.Such assays provide only a binary yes-no answer and cannot provide moreadvanced data, such as differentiation among different binding species.

Electrical detection methods have been based on potentiometric,piezoelectric, and capacitive systems. Potentiometric systems measurethe variation in the surface potential of an electrode or change indrain current of a transistor. These measurements tend to benon-specific. Piezoelectric systems measure the change in the mass ofmolecules bound to a quartz surface, but suffer from instabilities andproblems with calibration.

Capacitive measurements have been used for detection of DNA and cellstructures, such as U.S. Pat. No. 5,891,630 (Eggers et al.); U.S. Pat.No. 6,169,394 (Frazier et al.); and U.S. Pat. No. 5,846,708 (Hollis etal.). In these studies, the substrates have consisted of Si/SiO₂ ormetal electrodes coated with insulating material. These approachesfurther have focused on determination of a unique “resonance frequency”for a given molecule or complex.

Capacitive detection of antibodies and antigens bound to a sensorsurface has been reported. However, these electrical detectionapproaches have employed only a fixed frequency to detect relativechanges in the dielectric constant due to binding to the sensor surface.

BRIEF DESCRIPTION OF THE DRAWINGS

FIG. 1 is a diagram of an electrode module structured to directly detectelectrical parameters of a biomolecular electrode.

FIG. 2A is an enlarged top view of the module of FIG. 1, showinginterdigitated electrodes in a sample well on a substrate.

FIG. 2B is an enlarged cross-sectional view taken along line 2B—2B inFIG. 2A, showing electrode fingers with probe biomolecules adheredthereto.

FIG. 2C is an enlarged cross-sectional view similar to FIG. 2B, showingtarget biomolecules bound to the probe biomolecules adhered on electrodefingers.

FIG. 3 diagrams a first embodiment of a device for the direct electricaldetection of molecule—molecule interactions.

FIGS. 4A–4B are diagrams of an embodiment having a plurality ofinterdigitated electrode pairs arrayed on a chip.

FIGS. 5–8 are graphs presenting experimental results for anantibody-antigen pair, generated using an analyzer device and method asdescribed herein.

DETAILED DESCRIPTION OF PREFERRED EMBODIMENT(S)

The present disclosure describes detection of distinguishingcharacteristics of proteins and other biological compositions usingsignals spanning frequency ranges of several orders of magnitude.

General Arrangement of System

Turning to FIG. 1, an electrode module 10 for a bioelectrical circuitanalyzer 1 includes a substrate 11 with a sample well 12 formed thereon.The sample well 12 is and structured to receive a fluid test sample.

A circuit C (FIG. 3) has metal electrodes 14 positioned in contact withthe sample well 12 and formed in an apposed arrangement on the siliconsubstrate 11. Electrodes 14 preferably have interdigitated fingers 15(FIG. 2A) to increase the area of the electrodes 14 that are apposed.

The substrate 11 is a semiconductor, preferably constructed of siliconor a dielectric/insulator material. While the substrate 11 may be formedof a semiconductor, it is necessary that the region immediately adjacentthe electrodes be insulating relative to the capacitance of theelectrodes. This can be accomplished by oxidizing silicon in the regionsof the substrate 11 on which the electrodes 14 are deposited.

The metal electrodes 14 are constructed of a material that abiomolecular probe 30 (FIGS. 2A, 2B) can be adhered to. The probebiomolecule 30 can selectively bind a target biomolecule 30, e.g., anantibody probe and antigen target. The biomolecular probe 30 is adheredto at least one of the electrodes 14, and preferably multiple electrodes14, so as to coat same and impart a biochemical quality to the circuitC. Methods for adhering biomolecular probes to electrodes are discussedin greater detail, below.

In a preferred embodiment, at least one electrode 14 is constructed ofchromium. Alternative electrodes can be constructed of iridium, gold orsimilar metals. As well, a metal electrode can be plated with gold,chromium or other preferred metal.

The biomolecular probe includes a complexing biomolecule. Exemplarycomplexing biomolecules include proteins (e.g. an antibody),carbohydrates, lipids, hormones and other biomolecules capable offorming a complex with another moiety.

The bioelectrical circuit analyzer 1 of FIG. 3 further can have astimulator 20 electrically coupled to the circuit C. The stimulator 20is operative to provide an input alternating signal spanning a selectedfrequency range F₁–F₂. The selected frequency range F₁–F₂ can span arange of about 10⁻⁶ to 10⁶ Hz or higher. In preferred embodiments F₁ isequal to or less than about 10⁻² Hz or 10⁻³ Hz. The high-frequencyboundary F² of the selected frequency range F₁–F₂ preferably can beequal to or greater than about 10⁻⁴ Hz. The stimulator 20 and detector22 can be provided by a single, combined test instrument (e.g., animpedance analyzer as discussed below).

A detector 22 can be coupled to the circuit C. The detector 22 isstructured to detect and measure any one or more of a plurality ofelectrical parameters of the circuit C over the selected frequency rangeF₁–F₂. Parameters include phase, amplitude, dissipation factor,conductance and/or impedance.

By analysis of the detected electrical parameter(s), the detector 22further can generate an input signal profile for a given biochemicalcircuit, preferably digitized across the frequency range F₁–F₂. Thesignal profile is a unique “electro-fingerprint” of the testedbiochemical circuit, based on electrical parameter measurements at aplurality of points through the selected frequency range F₁–F₂.

The bioelectrical circuit analyzer 1 can include a comparator 24 (e.g.,a suitably programmed digital processor as shown in FIG. 3) operative tocompare the digitized output signal profile with a first digitizedreference signal profile to detect a match across the frequency range.Signal profiles produced by the analyzer 1, as well as reference signalprofiles, can be stored in a database accessible by the analyzer.

The comparator 24 further can be operative to detect a complexing eventof the probe biomolecule 30 and an unknown biomolecular target 32 in thefluid test sample introduced into the sample well 12. This detection canbe made on the basis of differences in the bioelectrical properties ofthe circuit. The biomolecular basis for fingerprinting, signal profilecomparison, and detection of biocomplexes is addressed more fully below.

The metal electrodes 14 are shown in greater detail in FIG. 2A. In thisrepresentative embodiment, interdigitated electrode fingers 15 are 1000um long, 1–5 um wide, and separated by a gap of 1–5 um. Dimensions ofmetal electrode fingers 15 can be varied without departing from theessential structure and function of the test cell disclosed herein.

The number of interdigitated electrode fingers 15 also can be varied.Prototype embodiments have incorporated from 100 to 500 electrodefingers 15, although a greater or lesser number can be efficaciouslyemployed.

To manufacture a representative test cell, a 2 um oxide layer was grownon a silicon substrate 11. Next, one or more wells 12 a–12 n were etchedin an oxide layer on the surface of the silicon substrate 11 (in anillustrative embodiment, wells are 4 mm×4 mm×1 um deep).

A high purity metal layer of 1.0 um thickness was then deposited on thesubstrate 11 (e.g., by using a sputtering machine). The interdigitatedelectrodes 15 were formed by first patterning (for example, usingphotolithography) and then etching off the unwanted metal layer so thatthe electrodes are formed in the well 12. Contacts for interdigitatedelectrodes 15 can be structured such that the contact pads 16 arepositioned outside the well 12 (FIG. 1).

In other embodiments, shown in FIG. 4A, the bioelectrical circuitanalyzer 1 can further include a plurality of sample wells 12 a–12 nformed on the substrate 11 and structured to receive a correspondingplurality of fluid test samples. A corresponding plurality of electrodes14 a–14 n can be arranged in an X-Y array to place an electrode incontact with each sample well.

Selection circuitry (X- and Y-axis addressing) connected to theelectrode contact pads 16 (FIG. 2A) is useful in these embodiments toallow a signal to be transmitted to a selected electrode. Selectioncircuitry can be built into a device portion of a silicon substrate 11.Contact pads 16 then can be coupled directly to the selection circuitryor other device region of the substrate 11.

In another alternative embodiment, a plurality of wells 12 a–12 n andinterdigitated electrodes 15 can be manufactured in an array (FIG. 4A).In such a sensor array, different probe biomolecules 30 can be attachedto interdigitated electrodes 15 in different sample wells 12 formed onmodule 10.

Using this approach, a wide range of intermolecular interactions can besimultaneously characterized in one bioelectrical circuit analyzer 1.Each set of electrodes 14 can be analyzed with its corresponding X_(n)and Y_(n) contact pads 16, disposed along the edge of the substrate 11as shown. Arrayed contact addressing is similar to that used in flatpanel display technology.

Adherence of Probe Biomolecules

A representative method is presented for adherence of probe biomoleculesto metal electrodes 14 of an analyzer 1, such as described above. Theelectrodes 14 of this example are composed of chromium.

A probe biomolecule was selected, e.g. a mouse IgG monoclonal antibodydirected against anti-human interferon-gamma. A small volume (e.g., 200ul) of monoclonal antibody solution was placed in a coating buffer iscontacted with the interdigitated electrodes 15 of the analyzer 1.Incubation time for attachment can be varied. Experiments have shownthat an incubation period as brief as 2 minutes is effective. Afterincubation, the well 12 is washed.

To assess adherence of the antibody to the electrodes 14, the abovemethod was performed using a biotin-conjugated antibody (2-minuteincubation), followed by a standard calorimetric assay. For comparison,the monoclonal antibody (mAb) probe biomolecules also were bound to aconventional plastic microtiter plate, as is commonly done in ELISAassays.

The well 12 was incubated for 20 minutes with streptavidin-conjugatedhorseradish peroxidase (HRP). An HRP substrate,3,3′,5,5′-tetramethylbenzidine (TMB), was then added and color allowedto develop for 2 minutes before the reaction was stopped. The testsolution was then transferred from the chip surface or fastwell to amicrotiter plate well and assessed for absorbance at 450 nm.

TABLE 1 Chip surface/Electrode Composition Net O.D. (corrected) Si/Cr1.344 Plastic Microtiter Plate (mAb-coated) 1.300 Si/Au 1.143 SiO₂/—0.167 Si/Al 0.079

Results of the calorimetric assay are presented in Table 1. These dataindicate that antibodies were attached to the Si/Cr embodiment betterthan to most other tested electrode compositions. A chromium electrodeproved most efficacious in binding antibody as compared with aluminumand SiO₂. High binding efficiency was observed for the chromiumelectrode, on a par with that of plastic microtiter ELISA plates.Binding to gold was acceptable but not as optimal as that to chromium.

It should be noted that, for the Si/Au electrode, the integrity of thegold electrode was suboptimal, with peeling of the electrode from thesurface of the substrate 11 seen when aqueous buffers were added. Thegold surface was stabilized when gold was coated over a chromiumelectrode base.

Data further indicate that approximately twice as much antibody wasbound to a Si/Ir chip as compared to the Si/Cr chip. Unfortunately, theiridium electrode was observed to have a background reactivity (with theenzyme alone) of roughly three times that of chromium.

The antibody concentration was titrated to determine the sensitivity ofdetection using the above-described 2-minute probe biomolecule adherenceprotocol. Antibody solutions were made up using 6 dilutions: 2,000ng/ml, 400 ng/ml, 80 ng/ml, 16 ng/ml, 3.2 ng/ml, and 0.64 ng/ml. Thesedilutions resulted in net O.D. readings of 0.763±0.065, 0.627+0.110,0.317±0.021, 0.064±0.006, 0.000±0.001, and 0.000±0.013, respectively.These results demonstrate that the sensitivity of detection of theantibody was about 16 ng/ml under these conditions.

Antibody binding is increased when the adherence protocol is performedin the presence of an electrical field. An electrode was devised thatallowed the substrate 11 to act as either the cathode (+polarity) oranode (−polarity). The antibody solutions, as using in the abovetitration assay, were placed in the sample well 12 and the electricalfield applied to the solution. The electrical conditions were set at 1mA direct current producing 2 V, and the incubation proceeded for 2 min.

TABLE 2 Antibody Conc. Net O.D. Δ(Net O.D.) Δ(Net O.D.) (ng/ml) No FieldChip as Cathode Chip as Anode 2,000 1.221 +0.269 (+22%) −0.025 (−2%) 4000.840 +0.200 (+24%) — 80 0.305 +0.086 (+28%) +0.025 (+8%) 16 0.076 +0.114 (+150%) Precipitated (0%)

The results of these experiments, using different concentrations ofantibody, are summarized in Table 2. These results indicate that theantibody binding is enhanced when the chip is positively charged,especially at lower protein concentrations. No additional binding wasobserved when the chip is negatively charged; in fact, a negative chargeproved non-optimal in some cases.

The use of a field with the substrate 11 as cathode therefore can bebeneficial in depositing low concentrations of probe biomolecules 30onto the electrodes 14. The sensitivity of detection of antibody withthe substrate 11 as cathode (<16 ng/ml) is equivalent to 100 pMantibody.

It is hypothesized that the presence of an alternating electric fieldorients probe molecules differently on the electrode surface than in astatic state. By way of example, antibodies are non-symmetric molecules;hence their polarization and their dielectric behavior will change whensubjected to an alternating input signal. The above variation of theprobe binding method (application of electric field during adherenceincubation) allows an additional parameter for electrically detectingmolecules and molecule—molecule interactions.

The antigen, in this example anti-human interferon-gamma to which themouse IgG monoclonal antibody was directed, was then added in each oftwo sample wells: a first sample well 12 with bare metal electrodes anda second well having an antibody-coated electrode. The MOPS buffer wasused to provide an acceptable chemical environment for antibody-antigenspecific binding.

Detection Methodology in General

The capacitance, dissipation factor, phase, conductance and/orimpedance, measured over the selected frequency range for theantibody-coated electrode, antibody-coated electrode with antigen insolution above, and biomolecular complex adhered to the electrode,therefore can provide unique fingerprints of these molecules andmolecule—molecule complexes.

The electrical character of the electrodes 14 of the biochemical circuitC can be electrically altered by an electro-molecular change in theprobe 30 or probe 30-target 32 complex adherent thereto. The change inelectro-molecular properties is caused by an applied signal of changingfrequency provided by a stimulator 20.

The measured electrical parameters are based on the fact that themolecules investigated are relatively large and are therefore believedto affect the dielectric value and the conduction of current across theelectrode gap.

The variable in the above example is the frequency of the alternatinginput signal. When an electric field is applied across a molecule, thereis a tendency for the charges on the molecule to align with this appliedfield. In larger molecules, the electron cloud surrounding thesemolecules often redistributes; hence, there is some charge separation ormolecular polarization.

The ability and rapidity of molecular charge separation depends on thestrength of the covalent and electrostatic bonds. Loosely-bound chargescan respond to the electric field at higher frequencies (e.g., 10² to10⁵ Hz); similarly, tightly-bound charges respond to the electric fieldat lower frequencies (e.g., 10⁻⁴ to 10⁰ Hz). Thus, by looking at theresponse over a frequency range, specific traits of a given molecule (orbiomolecular complex) can be examined.

The present approach can be carried out by examination of one or moreelectrical parameters. It can be anticipated that, for largebiomolecules displaying gross changes to changing frequency inputs, asingle parameter may be sufficient to perform identification. Forsmaller biomolecules or those exhibiting more subtle electro-signatures,a plurality of electrical parameters preferably are examined.

The applied field between the electrodes will transport a signal betweenthem. The transfer of charge between the electrodes across the gap willbe affected by the molecules attached to them. Consequently, theresistance or impedance behavior exhibited by the signal will depend onthe attached molecules and can be observed in the electrical parameterscan.

A capacitance scan permits examination of the dielectric response, whichwas observed to become dominant at lower frequencies. The dissipationfactor indicates the ratio of resistance to capacitive reactance betweenthe electrodes. Impedance or resistance also will induce a phasedifference between the applied voltage and the current. This phasedifference also can be measured.

A method for generating a signal profile for a biomolecule orbiomolecular complex entails first adhering a biomolecule, e.g. probebiomolecule 30, on an electrode 14 positioned on the conductivesubstrate 11.

An alternating input signal is applied to the electrode having probebiomolecules adherent thereon. The input signal includes a frequencyrange of from greater than 10⁻⁶ Hz to about 10⁶ Hz and preferably is analternating current.

Signal parameters are measured over the frequency range for a pluralityof electrical parameters of the electrode having a probe biomoleculeadherent thereon. The plurality of electrical parameters can includecapacitance, phase, dissipation, conductance and/or impedance. Inpreferred embodiments, the electrical parameters include all four ofcapacitance, phase, dissipation factor and impedance.

The measured signal parameters over the frequency range for the coatedelectrode are stored as a probe biomolecule electrical parameterprofile. The parameter profiles can be stored in a database, memory orother means. Parameter data can be measured over a frequency range thatis about two orders of magnitude within the selected frequency range,and further can be logically associated with the biomolecule.

The method can further include forming a biochemical complex on theelectrode 14 on the conductive substrate 11. The complex is formed bythe probe biomolecule 30, which has been adhered on the electrode, and atarget biomolecule 30 introduced into the sample well 12.

The biochemical complex can contain as one member a protein, such as anantibody or a glycoprotein; a hormone; a gene transcription regulatingcomponent; a polynucleotide; a carbohydrate; an immune system component;or other relevant biomolecule capable of complexing. For example, aspecific DNA sequence (i.e, probe biomolecule) can be adhered to theelectrode 14 and a gene transcription regulating protein introduced tothe sample well 12. The regulating component (i.e., target biomolecule)can bind to the adhered DNA sequence.

The pattern of electrical parameter changes further can be used tocorrelate the measured pattern of electrical parameter changes with aspecific biomolecular species in the liquid sample. Such correlation canbe used to detect and identify a specific target in a sample using atest cell having a plurality of different probes attached to theelectrodes thereof.

Generation of Reference Set

A reference set can be created, wherein each reference profile in theset is a profile of reference electrical parameter changes for abiochemical species. A generated sample profile can then be compared tothe members of the reference set. Because of the unique stereochemicalstructure of the probe, target, and probe-target complex, as well as theelectron distribution therein, the profile observed for a particularprobe-target complex is sufficiently distinctive that it can be used toidentify that complex.

A method for generating a biomolecule electrical parameter profiledatabase can proceed similarly. After adhering a probe biomolecule on anelectrode positioned on a conductive substrate, an alternating inputsignal is applied to the circuit. The input signal includes a frequencyrange of from greater than 10⁻⁶ Hz to about 10⁶ Hz.

Signal parameters are measured over the frequency range for a pluralityof electrical parameters of the electrode in the circuit, the electricalparameters including capacitance, phase, dissipation factor andimpedance.

Measured signal parameters over the frequency range are stored as aprobe biomolecule electrical parameter profile.

A reference profile for the bare metal electrode 14 can also begenerated, by applying an alternating input signal to an electrode freeof adherent probe biomolecules, and measuring and storing same as anelectrode electrical parameter profile.

In scaling up, a 2^(nd)–n^(th) probe biomolecule can be adhered on acorresponding 2^(nd)–n^(th) electrode positioned on at least a firstconductive substrate. Similarly, an alternating input signal then can beapplied to the 2^(nd)–n^(th) electrode, the input signal including afrequency range of two or more orders of magnitude selected from greaterthan 10⁻⁶ Hz to about 10⁶ Hz.

Measurement of signal parameters over the frequency range for aplurality of electrical parameters of the 2^(nd)–n^(th) electrode havingthe 2^(nd)–n^(th) probe biomolecule adherent thereon proceeds as above,the plurality of electrical parameters including capacitance, phase,dissipation factor, conductance and/or impedance. Measured signalparameters over the frequency range likewise are stored for theplurality of electrical parameters of the 2^(nd)–n^(th) electrode as the2^(nd)–n^(th) probe biomolecule electrical parameter profile.

The reference database further can contain one or more probe-targetbio-complex electrical parameter profiles. As described above,introduction of a target biomolecule into the sample well can form abio-complex with the probe biomolecule on the electrode.

Additionally, a 2^(nd)–n^(th) target biomolecule can be introduced toform a 2^(nd)–n^(th) biomolecular complex with the 2^(nd)–n^(th) probebiomolecule on the 2^(nd)–n^(th) electrode prior to applying thealternating input signal to the 2^(nd)–n^(th) electrode. Measured signalparameters over the frequency range are stored for the plurality ofelectrical parameters as the 2nd-n^(th) target biomolecule electricalparameter profiles.

Method Applied to Examples

A method is disclosed for analyzing a biochemical circuit having aliquid sample in contact with two interdigitated electrodes, wherein atleast one of the electrodes has probe biomolecules adhered thereto. Themethod includes contacting the sample with an electrode in a sample wellformed on a conductive substrate, thereby form a biochemical circuit.

An alternating input signal spanning a selected frequency range F₁–F₂ isapplied to the circuit and an output electrical parameter of thebiochemical circuit is measured over the frequency range, particularlyany change in response to the change in frequency.

A test sample profile can be generated from the measured electricalparameter and used to correlate the test sample profile to a referenceprofile in a database or set of reference profiles.

The test sample profile can be generated by creating a plurality of datapairs, wherein each pair includes a frequency of a discrete input signaland a measured output electrical parameter for that discrete inputsignal. The plurality of data pairs can be associated with the unknowncomponent in the liquid sample, and the associated data pairs stored.

Identification of an unknown component can be accomplished by comparisonof the generated sample profile to at least a portion of a plurality ofreference profiles in a reference profile database. The plurality ofreference profiles can include reference profiles of a knownreceptor-ligand complexes, non-complexed receptors of knownreceptor-ligand pairs, non-complexed ligands of known receptor-ligandpairs, or a combination of these types of reference profiles.

Results are presented below in which a representative method wasundertaken using antibodies and their respective antigens. A sweepingfrequency spanning about 5×10¹ Hz to 10⁷ Hz was applied to the boundantibody alone (probe biomolecule), bound target molecule or controlmolecule alone (target biomolecule), and to a target molecule solutionapplied to a test cell having antibody bound thereto (probe and targetbiomolecules, expected to join and form a bio-complex).

First, a drop (˜50 ul) of dilute buffer solution (e.g., 0.1 M MOPS) wasplaced in a sample well. Electrode tips were contacted with the contactpads of an interdigitated pair of chromium electrodes. An alternatingcurrent input signal was applied to the solution in the well (e.g.,using an HP4192A Impedance Analyzer (Hewlett-Packard, Denver, Colo.) ora Solartron 1260 Impedance Analyzer (Solartron, San Diego Calif.)),varying in frequency from 5 Hz to 13 MHz.

Background electrical parameters (capacitance, dissipation factor,impedance (or conductance) and phase) were recorded and an electrodereference profile produced. The buffer solution was removed and the wellrinsed.

A drop of a solution containing anti-dinitrophenol (DNP) murine IgG wasthen placed in the sample well. The antibodies were incubated for 1–5minutes, during which time the antibodies were adhered to the chromiumelectrodes.

Impedance, phase, dissipation, and capacitance frequency spectra of anantibody-coated test cell were then measured according to the methodsdescribed above. The detector used for these experiments again was anHP4192A Impedance Analyzer and Solarton 1260 Impedance Analyzer.

Two DNP-tagged target molecules (DNP-albumin and DNP-serine) and acontrol molecule (d-biotin) were used as target biomolecule in assays onan antibody-coated chromium electrode as described above. Phase andconductance data of the assays are shown in FIGS. 5–8. In each case,data were normalized to remove effects of the sample well and buffer.

FIGS. 5–6 present phase data for anti-DNP IgG with, respectively,DNP-albumin and DNP-serine in the fluid test sample. The phase parameteris the phase difference, in degrees, between the current and voltagethat occurs in a non-passive circuit. It can be seen that phase for eachmolecule varies with frequency, indicating that molecules are behavingas reactive components in the circuit. A zero phase difference impliesthat the molecules act passively in the circuit.

The antibody/DNP-albumin target complex (open pentagon) can be clearlydistinguished from bound antibody alone (black square), free DNP-albumintarget (open circle) and free d-biotin control target (open square) bydifferences in phase, and especially over the range of 10–100 Hz.

The phase data indicates that the antibody/target complex acts as anelectrically different molecular structure than bound antibody and freetarget in solution. Note that the line representing incubation of boundanti-DNP antibody with d-biotin (open square) does not have adistinctive peak at about 100 Hz, indicative of antibody specificity.

A second target molecule, DNP-serine, was used in related experiments(FIG. 6). Similarly to the results with DNP-albumin, a distinctive phasepeak was observed at about 10¹–10³ Hz (open diamond). A second peakoccurred at 10⁴–10⁶ Hz. This latter variation is absent from the datashown in FIG. 5 (compare to open pentagon).

When anti-DNP IGG alone is bound to the test cell electrode, it can beseen to yield consistent phase data (compare FIGS. 5–6). Conversely,DNP-albumin and DNP-serine are observed to produce readilydistinguishable plotted phase curves.

Conductance data for the above target biomolecules are shown in FIGS.7–8. The change in conductance of an test cell when anti-DNP IgGantibody bound its DNP-albumin target is clearly seen by acharacteristic dip at about 90 Hz and a slight dip at about 10⁷ Hz (FIG.7).

The line representing antibody/biotin control (open square) closelymatches that for bound antibody alone (black square), indicating thatbiotin remained free in solution and had little effect on theconductance of the circuit.

It is important to note that the conductance plot of anti-DNPIgG/DNP-serine complex bear gross similarity to that of anti-DNPIgG/DNP-albumin. However, the two curves can be differentiated based onthe strength and shape of the dips at about 10² Hz and about 10⁶ Hz.

It should further be appreciated that the phase and conductance data foranti-DNP IgG, whether alone or in the presence of d-biotin, are verynearly identical in all the experiments. This uniformity in electricalresponse occurred despite differing biomolecular milieu in the testsample solutions above the antibody-adhered electrode. As well,DNP-albumin and DNP-serine can be easily discriminated in the both phaseand conductance plots.

The uniform and repeatable electrical response of the probe biomolecule,combined with the unique “electro-fingerprint” of various targetbiomolecules, facilitates diagnostic as well as quantitativeapplications.

The device and method can be used to assay patient fluid samples for thepresence of a variety of substances. Tests can be performed to detect,for example, HIV sero-conversion or exposure to Varicella-Zoster orhepatitis viruses.

In addition, an antibody probe can be employed to detect and identify amicroorganismal target moiety. Exemplary target microorganisms include,e.g., Neisseria meningitidis, Streptococcus pneumoniae, or Haemophilusinfluenzae (bacterial meningitis); anthrax; smallpox; anddifferentiation of gram-negative and gram-positive bacteria.

Environmental samples similarly can be assayed to detect contaminationlevels in water supplies and other locations, including naturalcontamination and artificially-introduced contaminants (e.g., pollution,anthrax or smallpox as a result of terrorism).

For example, a probe molecule can be employed that specifically bindslead ions; electro-molecular changes induced by ion binding can bedetected by the analyzer and used to determine the presence of lead in asample.

It should be further apparent that the device and method disclosedherein are not limited to the representative antibody-antigen complexespresented. Indeed, the device can readily be used to detect interactionsof other molecular species. For example, protein—protein interactionscan be assessed with no significant change to the device or method.

As well, other molecular milieu can be assayed using a device and methodas disclosed herein. For example, deoxyribonucleic acids have beensuccessfully bound to the above-disclosed device using the method hereindisclosed. In one technique, a binding anchor was joined to one end of aDNA strand, such that the DNA strand could be adhered to the electrodewith the bulk of the DNA bases remaining free in the solution (i.e., thestrand adhered only at one end). The specific sequence of the DNA strandtherefore is available for hybridization to a complementary targetstrand. The present device therefore can be utilized in electricalcharacterization of annealed nucleic acid duplexes.

Moreover, the present test cell, device and method need not be limitedto use with biological molecules, but can be used to detect aerosol orsoluble chemical moieties, such as a toxic gas or evaporated acid, bythe effect of such moiety on an appropriately selected probe on the testcell.

Another feature of the present analyzer is the ability to train a neuralnetwork with the target biomolecule electrical parameter profiles. Oncethe frequency scans of the plurality of parameters are recorded, thisdata is fed to a neural network that will identify and store distinctivedata features. When an unknown molecule is subsequently analyzed, itsresponse will be compared to the stored data to identify it and/ordetermine its interaction with or relationship to the known moleculeadhered to the electrodes.

A person skilled in the art will be able to practice the presentinvention in view of the description present in this document, which isto be taken as a whole. Numerous details have been set forth in order toprovide a more thorough understanding of the invention. In otherinstances, well-known features have not been described in detail inorder not to obscure unnecessarily the invention.

While the invention has been disclosed in its preferred form, thespecific embodiments and examples thereof as disclosed and illustratedherein are not to be considered in a limiting sense. Indeed, it shouldbe readily apparent to those skilled in the art in view of the presentdescription that the invention can be modified in numerous ways. Theinventor regards the subject matter of the invention to include allcombinations and sub-combinations of the various elements, features,functions and/or properties disclosed herein.

1. A bioelectrical analyzer for identifying a biomolecular targetcomprising a protein or peptide, the analyzer comprising: a siliconsubstrate; a sample well formed on the substrate and structured toreceive a fluid test sample; an electrode formed within the sample wellof a metal having an exposed chromium surface to which proteins andpeptides are directly adherent and the chromium surface having adherentthereto a biomolecular probe capable of complexing with a biomoleculartarget, the biomolecular probe comprising a protein or a peptide; astimulator electrically coupled to the electrode and structured toprovide an input signal spanning a selected frequency test range F₁–F₂within the frequency range; a detector operative to detect a signal ofthe fluid test sample over the selected frequency test range andgenerate a sample signal profile for at least one sample electricalparameter across the selected frequency test range; and means forcomparing the sample signal profile with a first reference signalprofile to detect a match across the selected frequency test range. 2.The bioelectrical analyzer of claim 1 wherein the test sample includesan unknown biomolecular target comprising a protein or a peptide, andthe means for comparing is operative to detect a complexing event of theprobe and target.
 3. The bioelectrical analyzer of claim 1 wherein F₁ isequal to about 10⁻² Hz.
 4. The bioelectrical analyzer of claim 1 whereinF₂ is equal to or less than about 10⁶ Hz.
 5. The bioelectrical analyzerof claim 1 wherein F₂ is equal to or less than about 10³ Hz.
 6. Thebioelectrical analyzer of claim 1 wherein F₁ is less than 10² Hz.
 7. Thebioelectrical analyzer of claim 1 wherein the sample electricalparameter includes dissipation factor.
 8. The bioelectrical analyzer ofclaim 1 wherein the detector is operative to detect a plurality ofsample electrical parameters over the selected range of frequencies, theplurality of electrical parameters including phase and dissipationfactor.
 9. An electrode module according to claim 1 in which thesubstrate comprises a silicon substrate having a layer of siliconinsulative layer in which the sample well is formed, the chromiumelectrodes being formed on the silicon insulative layer within thesample well.
 10. An electrode module for use in a bioelectrical circuitanalyzer for identifying biomolecular target molecules comprising aprotein or a peptide, comprising: a silicon substrate; a sample wellformed on the substrate and structured to receive a fluid test sample;and a circuit element including chromium electrodes in contact with thesample well and having an exposed chromium surface, the surface havingadherent thereto a biomolecular probe comprising a protein or peptide.11. The electrode module of claim 10, further comprising a silicon oxidelayer between the silicon substrate and the chromium electrode.
 12. Theelectrode module of claim 10 wherein the chromium surface of theelectrode is coated with the biomolecular probe.
 13. The electrodemodule of claim 10 wherein the biomolecular probe includes a complexingbiomolecule.
 14. An electrode module according to claim 10 in which thesubstrate comprises a silicon substrate having a layer of siliconinsulative layer in which the sample well is formed, the chromiumelectrodes being formed on the silicon insulative layer within thesample well.
 15. An electrode module for a bioelectrical circuitanalyzer for identifying proteins and peptides, the module comprising: asilicon substrate; a sample well formed in the substrate and structuredto receive a fluid test sample; a pair of electrodes formed in thesample well in opposed spaced-apart relationship to receive the testsample between the electrodes; and means for coupling the electrodes toa stimulator to apply an electrical signal to the electrodes and sampleand to a detector operative to detect an electrical parameter of thesignal applied to the sample; the electrodes comprising chromium havingan exposed surface so that a protein or peptide is adherent directly tothe electrodes.
 16. An electrode module according to claim 15 in whichthe electrodes are formed in an interdigitated relationship.
 17. Anelectrode module according to claim 15 in which probe moleculescomprising the protein or peptide are adhered directly to theelectrodes.
 18. An electrode module according to claim 17 in which theprobe molecules consist essentially of antibodies.
 19. An electrodemodule according to claim 17 in which the probe molecules consistessentially of antigens.
 20. An electrode module according to claim 15in which the substrate comprises a silicon substrate having a layer ofsilicon insulative layer in which the sample well is formed, thechromium electrodes being formed on the silicon insulative layer withinthe sample well.
 21. An electrode module according to claim 20,including a plurality of said sample wells, each containing a pair ofsaid electrodes, the electrodes of each well being coupled to selectioncircuitry for connection to the stimulator and detector.